US4800884A - Magnetic induction hearing aid - Google Patents

Magnetic induction hearing aid Download PDF

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Publication number
US4800884A
US4800884A US06837708 US83770886A US4800884A US 4800884 A US4800884 A US 4800884A US 06837708 US06837708 US 06837708 US 83770886 A US83770886 A US 83770886A US 4800884 A US4800884 A US 4800884A
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Prior art keywords
magnet
means
hearing aid
coil
hydroxyapatite
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Expired - Lifetime
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US06837708
Inventor
Jorgan Heide
Timothy D. Gooch
Anthony D. Prescott
Thomas W. Sander
Jim Davidson
Eric A. Renz
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Gyrus Ent LLC
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Richards Medical Co
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    • HELECTRICITY
    • H04ELECTRIC COMMUNICATION TECHNIQUE
    • H04RLOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00Deaf-aid sets providing an auditory perception; Electric tinnitus maskers providing an auditory perception
    • H04R25/60Mounting or interconnection of hearing aid parts, e.g. inside tips or housing. to ossicles
    • H04R25/604Arrangements for mounting transducers
    • H04R25/606Arrangements for mounting transducers acting directly on the eardrum, the ossicles or the skull, e.g. mastoid, tooth, maxillary or mandibular bone, or mechanically stimulating the cochlea, e.g. at the oval window

Abstract

A magnetic induction hearing aid where the microphone, the amplifying electronics, the battery and a coil are contained in a single housing which is located deep in the ear canal. A magnet is attached to portions of the middle ear by means of a malleus clip or by implantation between the tympanic membrane and the malleus. The magnet is vibrated by interaction with the magnetic field produced by the coil. Two amplifier designs are disclosed for use with different levels of hearing loss. The magnet can be coated with hydroxyapatite for permanent attachment to the body. The magnet is coated with hydroxyapatite by an ion implantation process, a plasma spraying technique or a method of applying the hydroxyapatite while a precoating polymeric material has not fully solidified.

Description

BACKGROUND OF THE INVENTION

1. Field of the Invention

The present invention relates to hearing aids and, more particularly, to a hearing aid using magnetic induction to reproduce sound.

2. Description of the Prior Art

Hearing aids are useful in restoring lost aural perception to those persons having mild or severe loss of hearing. Conventional hearing aids have a microphone, amplifier circuitry, a battery and a speaker. The microphone receives the sound energy and transforms the sound energy into an electrical signal which is then amplified and filtered. This amplified signal is transformed back to acoustic energy by the speaker and transmitted to the person's middle ear for perception of the sound. These hearing aids can be placed behind the ear, with only the receiver being placed inside the ear canal. Alternatively, in-the-ear hearing aids are available which are placed in the outer ear and have portions extending into the ear canal.

There are a number of problems with conventional hearing aids. All conventional hearing aids are visible to some extent and therefore have an undesirable cosmetic appearance. Conventional hearing aids have acoustic feedback problems because sound energy can escape from the ear canal and be detected by the microphone, generating a feedback-related whistle. Additionally, sound reproduction is often lacking in clarity because of distortions generated by standing waves existing in the closed cavity between the hearing aid and the tympanic membrane and poor mechanical reproduction by the speaker.

It has been suggested that a magnetic induction hearing aid would remove many of these problems. A magnet or other item having a magnetic field is placed in the middle ear, either in contact with the tympanic membrane or in contact with other portions of the middle ear. Electrical circuitry and a coil would generate a magnetic field having the same frequency as the external sound. The magnetic field generated by the coil would interact with the field of the magnet and cause the magnet to vibrate at the same frequency as the magnetic field. The vibration of the magnet would then cause the attached portion of the middle ear to vibrate, resulting in a perception of the external sound.

A magnetic induction hearing aid would overcome feedback or distortion problems of conventional hearing aids because there would be no significant air movement in the ear canal, resulting in insufficient energy escaping around the hearing aid to generate a feedback problem. There would be no standing waves generated to cause distortion because there are no appreciable sound waves at all.

Attempts to use magnetic induction hearing aids have been reported. An early attempt placed a coil in conjunction with a small piece of iron on the tympanic membrane, which was excited by an external coil placed over the ear canal. This system did allow the perception of the stimulus, but had the side effect of producing discomfort and pain for the wearer. A later attempt glued a small magnet to the umbo and used an external coil placed over the ear of the wearer to cause the sympathetic vibrations of the magnet. This apparatus required approximately 7.9 ma to produce a 0 db hearing level at 1000 Hz.

In an article entitled Audition via Electromagnetic Induction, Arch Otolaryngol 23 (July 1973), Goode et al describe a number of tests. One test attached a magnet to the tympanic membrane and located a coil in the ear canal 3 mm from the magnet. The coil was driven externally by an audiometer. This development required only 0.7 μa to produce a 0 db hearing level at 1000 Hz. Tests were performed for system fideltiy and proved adequate. Another system tested placed the coil over the ear, drove the coil with an audiometer and had a magnet glued to portions of the middle ear, but used larger magnets than in previous tests. One version of this system placed the magnet on a Silverstein malleus clip which was connected in the normal manner. Approximately 0.7 ma was required to produce a 0 db hearing level using these arrangements.

These discussions suggested that the use of electromagnetic induction to produce a hearing aid is possible, but did not teach a way to develop a practical system. The majority of tests used coils placed over the ear or adjacent to the ear. Systems using external coils are not efficient enough for use in conjunction with the low power requirements dictated by hearing aid batteries. Although one test indicated that a coil was placed inside the ear canal, an external amplifier was used to drive the coil. The tests did not result in a practical device or suggest how a totally in-the-ear device could be made.

Further, the magnets described in conjunction with the above-mentioned tests were either glued to portions of the middle ear and removed after short periods of time or were connected to malleus clip and inserted for a longer duration. Neither of these attempts resulted in a magnet that could be implanted for extended periods of time with no danger of rejection by the body, have no movement in relation to the middle ear and yet have as little weight as possible.

SUMMARY OF THE INVENTION

The present invention is directed to a magnetic induction, in-the-ear hearing aid where all the elements of the hearing aid are placed within the ear canal and the middle ear. A microphone, amplifying electronics, battery and driving coil are placed within a single housing which is custom molded for each wearer and placed deep within the ear canal. A magnet can either be mounted on a Silverstein malleus clip and connected to the malleus or coated with hydroxyapatite or similar material that allows tissue in the eardrum to adhere to the magnet and installed between the eardrum and the malleus.

The amplifier is one of two types, either Class A or Class B, depending on volume levels required. The coils are matched to the particular amplifier type to provide optimal efficiency for a given design. The coil is formed of a number of turns of wire wound over a mumetal core, which is used to increase magnetic field strength. The coil is placed close to the magnet to allow optimal coupling of the magnet's field with the magnetic field produced by the coil.

The magnet is formed of a neodymium-iron material allowing a very high strength magnetic field to be developed by a very small magnet. Since this material corrodes when placed in an animal body, it is coated with a biocompatible material if the magnet is installed on a Silverstein malleus clip for connection to the middle ear.

Alternatively, if the magnet is implanted behind the tympanic membrane, it can be coated with hydroxyapatite or other material that protects the magnet from corrosion and allows the magnet to become permanently bonded to the body by the adherence of body tissue to the hydroxyapatite. The magnet may have an underlying coating of other bio-compatible materials so that the magnet is sealed and to allow the hydroxyapatite to better adhere to the magnet. This initial coating or precoat of the magnet can be formed of gold or a number of biocompatible polymers.

The hydroxyapatite can be applied using an ion implantation technique to allow the coating to be performed at low temperatures, which are necessary to prevent demagnetization of the magnet. An alternative process for applying the hydroxyapatite is a plasma spraying technique where the magnet is kept sufficiently cool to prevent demagnetization. Yet another method for applying the hydroxyapatite involves depositing the hydroxyapatite on the magnet surface before the polymer coating is completely solidified.

BRIEF DESCRIPTION OF THE DRAWINGS

A better understanding of the invention can be obtained when the detailed exemplary embodiment set forth below is considered in conjunction with the following drawings, in which:

FIG. 1 is a cross-sectional view of a human ear with a magnetic induction hearing aid according to the present invention placed in the ear canal;

FIG. 2 is an electrical schematic diagram of one embodiment of a circuit utilizing a Class A amplifier designed according to the present invention;

FIG. 3 is an electrical schematic diagram of a second embodiment of a circuit utilizing a Class B amplifier designed according to the present invention;

FIG. 4 is a side view of a malleus clip having a magnet mounted thereon;

FIGS. 5a, 5b, 5c and 5d are, respectively, cross-sectional top and side views of a magnets formed according to the present invention;

FIG. 6 is a partial cross-sectional view of a middle ear showing an magnet implanted according to the present invention;

FIG. 7 is a cross-sectional view of an eardrum or tympanic membrane and malleus in which a magnet mounted to a malleus clip is connected to the malleus; and

FIGS. 8a, 8b and 8c are schematic illustrations of coils formed according to the present invention.

DETAILED DESCRIPTION OF EXEMPLARY EMBODIMENTS

Referring to FIG. 1, the letter H refers generally to a hearing aid according to the present invention and is shown installed in an ear canal 34. The hearing aid H has a housing 30 enclosing a microphone 20, an amplifier 22, a volume control 24, a battery 26 and a coil 28. The hearing aid H is located deep in the ear canal 34 so that the coil 28 is located near a coated magnet 32, with 2.5 mm being a desirable distance for this separation. This distance is sufficiently close to reduce the inverse relationship of distance to magnetic field strength and yet is sufficiently far that the hearing aid H can be inserted by the wearer with minimal difficulty and not be in danger of contacting the tympanic membrane 68.

The installation of the hearing aid H deep within the ear canal 34 as shown in FIG. 1 eliminates any negative cosmetic effects of a hearing aid because the hearing aid H is practically undetectable. A conventional hearing aid cannot be inserted this deep in the ear canal 34 because of the standing wave and feedback problems discussed above. These problems do not occur in a magnetic induction hearing aid and therefore this deep placement is possible.

Volume adjustment and battery replacement is accomplished by removing hearing aid H from the ear canal 34, appropriately adjusting the volume control 24 or replacing the battery 26 and reinserting the hearing aid H into the position shown in FIG. 1.

The housing 30 is custom molded to each wearer's ear canal 34. This is necessary because each wearer has a differently sized and shaped ear canal. The hearing aid H must be sufficiently close to the magnet 32 for proper operation and the hearing aid H must be sufficiently tight within the ear canal 34 to remain in place during normal use.

A class A amplifier design is shown in FIG. 2. The microphone 20 is a standard electret microphone as conventionally used in hearing aids. The amplifier 22c is class A design that is standard in hearing aid applications. This amplifier is specifically designed for low voltage operation in conjunction with a single 1.3 volt battery. The volume control 24 is connected to vary the gain of the amplifier 22c and thereby change the output signal level applied to the coil 28a. The coil 28a is designed for use with the class A amplifier 22c.

Each amplifier used in hearing aids has a recommended output load impedance which is normally deemed to be the speaker or receiver impedance. For optimum performance of the hearing aid H, the coil 28a should be designed to match this characteristic desired impedance across as wide a frequency band as possible. The coil 28a is a double-ended coil designed to be connected to the battery 26 and to the output of the amplifier 22c. The coil 28a is formed by winding the appropriate number of turns of wire 72 (FIG. 8a) about a high permeability core 70. Preferably, the core 70 is comprised of mumetal to increase the magnetic field strength at the ends of the coil. The maximum coil size is preferably approximately 9 mm long and 4 mm in diameter. This size limitation is used in conjunction with the optimum coil impedance in determining the number of turns of wire 72 and the gauge of the wire 72 to produce a coil of the allowed size having the desired impedance.

The class A amplifier 22c is used in situations where the wearer has only a mild to moderate loss of hearing. The class A design is used in the mild loss case because the power consumption of the class A amplifier 22c is lower, but the maximum output is also lower, necessitating a higher performance or class B design for high power needs.

Where the wearer has a more severe hearing loss requiring greater amplification of the sound signal, what is known as a class B amplifier design as shown in FIG. 3 is used. A class B amplifier 22b is used in the higher volume, higher amplification situations because it has a power output level higher than that of the class A amplifier 22c. The trade off for this efficiency is reduced battery life because of the higher current draw of the class B amplifier design.

The microphone 20 is connected to a preamplifier stage 22a through an impedance matching and filter stage 38. The class A preamplifier 22a provides a fixed amount of gain and produces an output signal which is transmitted to filter capacitors 42 and 44 and the volume control 24. Appropriately adjusting the volume control 24 changes the output voltage of the class B output amplifier 22b which in turn drives coil 28b. As in the class A amplifier 22c, the class B output amplifier 22b has an optimal load impedance resistor which is specified by the manufacturer. The coil 28b is designed to have an impedance which matches this optimal impedance over as broad a frequency band as is necessary for the given application. The coil 28b is designed with a center tap (FIGS. 8b and 8c) to allow use with the class B amplifier 22b. An appropriate number of turns of the appropriate gauge wire 74 are wound around the mumetal core 70 or other high permeability material and connected as required to the amplifier 22b. The class B amplifier 22b produces greater power because of its class B design and its push-pull operation, enabling the coil 28b to produce larger magnetic field densities and thereby move the magnet 32 a greater distance.

The coil 28 produces a magnetic field varying at the frequency of the sound waves received by the microphone 20. The coil's magnetic field then interacts with the magnet 32. A sympathetic vibration of the magnet 32 occurs at the frequency of the sound waves. This mechanical vibration of the magnet 32 is then translated into movement of either the malleus 36 if the magnet 32 is attached to a malleus clip 60 (FIG. 7) or to vibration of the malleus 36 and the tympanic membrane 68 if the magnet 32 is inserted between the malleus 36 and the tympanic membrane 68 as shown in FIG. 6.

It is desirable that the coil 28 be placed in close proximity to the magnet 32 because a magnetic field decreases with strength according to an inverse law. Therefore, the coil's magnetic field effecting and interacting with the magnet 32 is radically diminished as the separation distance increases. This diminishing interaction directly effects the efficiency of the hearing aid H and therefore a minimum gap is desirable.

If the magnet 32 is implanted behind the tympanic membrane 68, the magnet 32 can move by either of two actions. The first movement is a piston-type action perpendicular to the plane of the membrane 68. The second action of the magnet 32 is a rocking action about a horizontal axis of the magnet 32. This rocking does cause the tympanic membrane 68 and the malleus 36 to vibrate, creating a sensation of sound. The rocking action is preferable because there is better magnetic coupling between the magnet 32 and the coil field, which increases effective acoustic gain and thereby system efficiency.

To aid generation of the rocking action of the magnet 32, it is preferable that the coil axis be at an angle, preferably 45 degrees, to the plane of the magnet 32. Lesser angles increase the likelihood of the less desirable piston action, while greater angles reduce magnetic coupling because of the shape of the coil's magnetic field.

The mass of the magnet 32 must be kept at a minimum to further increase the efficiency of the design so that the coil's magnetic field does not have to oscillate a larger mass and therefore require a larger energy transfer between the coil 28 and the magnet 32. But the magnet 32 must also be high strength so that the two interacting magnetic fields, the coil field and the magnet field, are sufficiently strong to create a large amount of coupling between the two fields. For this reason it is preferable that the magnet 32 be formed from the neodymium-iron which has an extremely high field strength for a given magnet size.

Because the magnet 32 is to be inserted in the human body it is necessary that the magnet 32 or magnet assembly be biocompatible and not corrode when placed in the body. It is also desirable that the magnet become firmly and permanently attached to the desired portions of the middle ear.

The preferred neodymium-iron magnet, in and of itself, does not meet these requirements. It corrodes when placed in the body and therefore is not suitable in its uncoated state for long-term placement or installation. Therefore, for biocompatibility the magnet 32 must be coated and sealed with a biocompatible material. There are two alternative versions of the coated magnet 32, one for use with malleous clip 60 and the other for direct implantation between the tympanic membrane 68 and the malleous 36.

The magnet 32 that is attached to the malleous clip 60 (FIG. 4) need only be biocompatible such that it does not produce an infection and does not corrode. For this use, a coating of the magnet with biocompatible materials such as gold or other nonresorbable, biocompatible material such as various commonly available polymers is necessary. No actual mechanical bonding between the magnet 32 and portions of the middle ear is necessary because the malleous clip 60 provides the connection with the malleous 36 and the magnet 32 is firmly mounted on the malleous clip 60.

For the embodiment of the magnet 32 to be used for direct implantation between the tympanic membrane 68 and the malleous 36, different criteria must be considered. It is highly desirable that this magnet 32 be coated with a bioactive material which will form a permanent bond with the middle ear. To this end it is preferable that the magnet 62 (FIGS. 5a, 5b, 5c, 5d) be coated with hydroxyapatite 64. Hydroxyapatite is a calcium phosphate material which has a particular crystal structure which resists biodeterioration and has an outer surface that easily adheres to tissue that is generated by the adjacent body portion.

Hydroxyapatite is preferred as the material that is useable as an outer coating material, but other nonresorbable bioactive materials could be used. Hydroxyapatite is referred to in this specification because it is the preferred material at this time and references to hydroxyapatite are intended to include other similar materials. Coating the magnet 62 with hydroxyapatite 64 and placing the coated magnet 32 between the tympanic membrane 68 and the malleous 36 results in the magnet 32 becoming part of the middle ear after a period of time due growth of middle ear tissue and its adherance to the hydroxyapatite coating 64.

A coating of hydroxyapatite 64 over a bare magnet 62 might possibly be satisfactory if the magnet were sealed from surrounding body fluids. However, because a neodymium-iron magnet is highly corrodable in an animal body and a complete seal is difficult to achieve, the magnet 62 first receive a precoating 66 prior to the final coating of hydroxyapatite 64. This precoating 66 is used to seal the magnet 62 from the bodily environment and therefore resist corrosion. The sealant can be a biocompatible material such as gold or other biocompatible polymers as are used in implantable medical devices. The precoated magnet is then coated with the hydroxyapatite 64 or other nonresorbable bioactive materials with similar properties.

There are several different processes that could be used for applying the hydroxyapatite coating. The first process is an ion implantation or sputtering technique where the target magnet is placed inside a vacuum chamber and positioned near a hydroxyapatite source. The hydroxyapatite source is then bombarded by an electron beam source from an ion accelerator so that the hydroxyapatite atoms are stripped from the source material and attracted to the target material due to electrostatic forces. Alternatively, a hydroxyapatite plasma can be produced by a radio frequency power source and directed toward the target material. The charged hydroxyapatite atoms are then driven into the magnet 62 or the precoat 66 by means of an accelerated argon ion beam. This firmly implants the hydroxyapatite atoms into the magnet 62 or precoat 66 forming a firm bond between the two layers. This process is continued until a sufficient hydroxyapatite coating thickness is produced, preferably about one micron.

The ion implantation process is a low temperature process which allows the magnet 62 to retain its magnetism. If the magnet 62 is subjected to a sufficiently high temperature, it loses its magnetism and therefore is rendered unusable. For this reason, the target must be kept at a low temperature which is capable of being done in the ion implantation or sputtering technique.

A low temperature process is also important so that the hydroxyapatite source material retains its hydroxyapatite structure. If the materials forming the hydroxyapatite are elevated to a sufficiently high temperature, the hydroxyapatite converts to tricalciumphosphate which is a bioresorbable material and is not satisfactory for coating the magnet 62. This is because the material is resorbed by the body and would eventually disappear from the magnet 62, leaving the magnet 62 uncoated and not bonded as desired. Therefore the low temperature ion implantation technique allows the hydroxyapatite 64 to keep its structure after being sputtered on the target magnet.

A second process for coating the precoated magnet is a plasma spraying technique. In this process the hydroxyapatite 64 is in the form of a powder and is fed through an argon plasma which melts the hydroxyapatite powder which is then fired onto the surface of the target magnet. The hydroxyapatite 64 then cools down, solidifies and is bonded to the precoating material 66. In this process it is possible to keep the substrate or target material temperature sufficiently low so as not to demagnetize the magnet 62.

A third process for applying the hydroxyapatite coating material involves placing the hydroxyapatite material on the surface of the polymer used as the precoat 66 before the polymer precoating material is fully solidified. When the biocompatible precoating polymer material 66 is applied to the magnet 62 in a molten form there is an interval wherein the precoating material 66 is sufficiently adhered to the magnet 62 and yet is not completely solidified. During this tacky or partially fluid state, the hydroxyapatite material is introduced onto the magnet assembly and physically pressed into the precoating material 66, therefore bonding with the precoating material 66 which then completes its hardening process. In this way, the hydroxyapatite material 64 has fully interlaced with the precoating polymer 66 which is firmly attached and sealing the magnet 64. An intermediate biocompatible coating attached to the underlying precoating material 66 can also be used to bond the hydroxyapatite 64 to the magnet 62.

The foregoing disclosure and description of the invention are illustrative and explanatory of the invention, and various changes in the size, shape and materials, as well as in the details of the illustrated construction and process may be made without departing from the spirit of the invention, all of which are contemplated as falling within the scope of the appended claims.

Claims (12)

We claim:
1. A magnetic induction hearing aid, comprising:
housing means with an outer surface shaped and dimensioned to fit entirely in an animal ear canal;
microphone means located in said housing means for producing an electrical signal in response to received sound waves;
amplifier means located in said housing means for amplifying said microphone means signal;
electrical power means located in said housing means for powering said amplifier means;
magnetic coil means located in said housing means and driven by said amplifier means for producing a magnetic field indicative of the received sound waves;
magnet means affixed to a portion of the middle ear and
wherein the magnet means is induced into movement by the magnetic field produced by the coil means such that the magnet means produces movement of the middle ear indicative of the received sound waves.
2. The hearing aid of claim 1, wherein the magnet means includes means for connecting the magnet means to the tympanic membrane.
3. The hearing aid of claim 1, wherein the magnet means includes a malleous clip which is adapted to clip to the malleous of the middle ear.
4. The hearing aid of claim 1, wherein the amplifier means comprises a class A amplifier.
5. The hearing aid of claim 1, wherein the amplifier means comprises a class B output stage and the coil means comprises a center tapped coil.
6. The hearing aid of claim 1, wherein the longitudinal axis of the coil means is oriented at an angle to the plane of the magnet means.
7. The hearing aid of claim 6, wherein said angle is 45 degrees.
8. The hearing aid of claim 1, wherein the magnet means is formed of neodymium and iron.
9. The hearing aid of claim 1, wherein the magnet means includes an outer coating formed of hydroxyapatite.
10. The hearing aid of claim 9, further including a precoating material under the outer coating for sealing the magnet means.
11. The hearing aid of claim 1, wherein the coil means comprises a high permeability core material and a plurality of turns of wire.
12. The hearing aid of claim 11, wherein the core material is formed of mumetal.
US06837708 1986-03-07 1986-03-07 Magnetic induction hearing aid Expired - Lifetime US4800884A (en)

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Application Number Priority Date Filing Date Title
US06837708 US4800884A (en) 1986-03-07 1986-03-07 Magnetic induction hearing aid

Applications Claiming Priority (8)

Application Number Priority Date Filing Date Title
US06837708 US4800884A (en) 1986-03-07 1986-03-07 Magnetic induction hearing aid
DE19873788529 DE3788529D1 (en) 1986-03-07 1987-03-06 A magnetic induction hearing aid.
DE19873788529 DE3788529T2 (en) 1986-03-07 1987-03-06 A magnetic induction hearing aid.
JP5042587A JPS63159000A (en) 1986-03-07 1987-03-06 Magnetic induction hearing aid
CA 531359 CA1277761C (en) 1986-03-07 1987-03-06 Magnetic induction hearing aid
EP19870301953 EP0242038B1 (en) 1986-03-07 1987-03-06 Magnetic induction hearing aid
US07050909 US4817607A (en) 1986-03-07 1987-05-15 Magnetic ossicular replacement prosthesis
US07050940 US4840178A (en) 1986-03-07 1987-05-15 Magnet for installation in the middle ear

Related Child Applications (2)

Application Number Title Priority Date Filing Date
US07050940 Continuation-In-Part US4840178A (en) 1986-03-07 1987-05-15 Magnet for installation in the middle ear
US07050909 Continuation-In-Part US4817607A (en) 1986-03-07 1987-05-15 Magnetic ossicular replacement prosthesis

Publications (1)

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US4800884A true US4800884A (en) 1989-01-31

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US06837708 Expired - Lifetime US4800884A (en) 1986-03-07 1986-03-07 Magnetic induction hearing aid

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US (1) US4800884A (en)
EP (1) EP0242038B1 (en)
JP (1) JPS63159000A (en)
CA (1) CA1277761C (en)
DE (2) DE3788529D1 (en)

Cited By (50)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4957478A (en) * 1988-10-17 1990-09-18 Maniglia Anthony J Partially implantable hearing aid device
US5015224A (en) * 1988-10-17 1991-05-14 Maniglia Anthony J Partially implantable hearing aid device
US5259032A (en) * 1990-11-07 1993-11-02 Resound Corporation contact transducer assembly for hearing devices
US5425104A (en) * 1991-04-01 1995-06-13 Resound Corporation Inconspicuous communication method utilizing remote electromagnetic drive
US5456654A (en) * 1993-07-01 1995-10-10 Ball; Geoffrey R. Implantable magnetic hearing aid transducer
US5554096A (en) * 1993-07-01 1996-09-10 Symphonix Implantable electromagnetic hearing transducer
US5624376A (en) * 1993-07-01 1997-04-29 Symphonix Devices, Inc. Implantable and external hearing systems having a floating mass transducer
US5797834A (en) * 1996-05-31 1998-08-25 Resound Corporation Hearing improvement device
US5800336A (en) * 1993-07-01 1998-09-01 Symphonix Devices, Inc. Advanced designs of floating mass transducers
US5897486A (en) * 1993-07-01 1999-04-27 Symphonix Devices, Inc. Dual coil floating mass transducers
US5913815A (en) * 1993-07-01 1999-06-22 Symphonix Devices, Inc. Bone conducting floating mass transducers
WO1999053971A1 (en) * 1998-04-17 1999-10-28 University College London Bone implant
US5993376A (en) * 1997-08-07 1999-11-30 St. Croix Medical, Inc. Electromagnetic input transducers for middle ear sensing
US6071527A (en) * 1996-04-10 2000-06-06 Asahi Kogaku Kogyo Kabushiki Kaisha Deodorant microphone cover and method of producing the same
US6123660A (en) * 1998-09-03 2000-09-26 Implex Aktiengesellschaft Hearing Technology Partially or fully implantable hearing aid
US6208740B1 (en) 1997-02-28 2001-03-27 Karl Grever Stereophonic magnetic induction sound system
US6264603B1 (en) 1997-08-07 2001-07-24 St. Croix Medical, Inc. Middle ear vibration sensor using multiple transducers
US6277148B1 (en) 1999-02-11 2001-08-21 Soundtec, Inc. Middle ear magnet implant, attachment device and method, and test instrument and method
FR2806630A1 (en) * 2000-03-22 2001-09-28 Iris Laboratoire Implantable prosthesis component e.g. for eye socket is made from biocompatible substrate covered with porous ceramic and nutrient layers
US6436028B1 (en) 1999-12-28 2002-08-20 Soundtec, Inc. Direct drive movement of body constituent
US6517476B1 (en) 2000-05-30 2003-02-11 Otologics Llc Connector for implantable hearing aid
US6676592B2 (en) 1993-07-01 2004-01-13 Symphonix Devices, Inc. Dual coil floating mass transducers
US6689045B2 (en) 1998-09-24 2004-02-10 St. Croix Medical, Inc. Method and apparatus for improving signal quality in implantable hearing systems
US20050065603A1 (en) * 2003-09-19 2005-03-24 Clarity Corporation Stapedial prosthesis and method of implanting the same
US20060189841A1 (en) * 2004-10-12 2006-08-24 Vincent Pluvinage Systems and methods for photo-mechanical hearing transduction
US20060251278A1 (en) * 2005-05-03 2006-11-09 Rodney Perkins And Associates Hearing system having improved high frequency response
US20090092271A1 (en) * 2007-10-04 2009-04-09 Earlens Corporation Energy Delivery and Microphone Placement Methods for Improved Comfort in an Open Canal Hearing Aid
US20090097681A1 (en) * 2007-10-12 2009-04-16 Earlens Corporation Multifunction System and Method for Integrated Hearing and Communication with Noise Cancellation and Feedback Management
US20090187233A1 (en) * 2008-01-18 2009-07-23 Stracener Steve W Connector for implantable hearing aid
US20100048982A1 (en) * 2008-06-17 2010-02-25 Earlens Corporation Optical Electro-Mechanical Hearing Devices With Separate Power and Signal Components
US20100152527A1 (en) * 2008-12-16 2010-06-17 Ear Lens Corporation Hearing-aid transducer having an engineered surface
US20100272299A1 (en) * 2007-10-30 2010-10-28 Koenraad Van Schuylenbergh Body-worn wireless transducer module
US20100312040A1 (en) * 2009-06-05 2010-12-09 SoundBeam LLC Optically Coupled Acoustic Middle Ear Implant Systems and Methods
US20100317914A1 (en) * 2009-06-15 2010-12-16 SoundBeam LLC Optically Coupled Active Ossicular Replacement Prosthesis
US20110082327A1 (en) * 2009-10-07 2011-04-07 Manning Miles Goldsmith Saline membranous coupling mechanism for electromagnetic and piezoelectric round window direct drive systems for hearing amplification
US20110125222A1 (en) * 2009-06-24 2011-05-26 SoundBeam LLC Transdermal Photonic Energy Transmission Devices and Methods
US20110144719A1 (en) * 2009-06-18 2011-06-16 SoundBeam LLC Optically Coupled Cochlear Implant Systems and Methods
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US8396239B2 (en) 2008-06-17 2013-03-12 Earlens Corporation Optical electro-mechanical hearing devices with combined power and signal architectures
US20130138213A1 (en) * 2001-05-11 2013-05-30 Exogenesis Corporation Medical device for bone implant and method for producing such a device
US8715154B2 (en) 2009-06-24 2014-05-06 Earlens Corporation Optically coupled cochlear actuator systems and methods
US8715153B2 (en) 2009-06-22 2014-05-06 Earlens Corporation Optically coupled bone conduction systems and methods
US8824715B2 (en) 2008-06-17 2014-09-02 Earlens Corporation Optical electro-mechanical hearing devices with combined power and signal architectures
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Families Citing this family (23)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4840178A (en) * 1986-03-07 1989-06-20 Richards Metal Company Magnet for installation in the middle ear
US4817607A (en) * 1986-03-07 1989-04-04 Richards Medical Company Magnetic ossicular replacement prosthesis
DE8816422U1 (en) * 1988-05-06 1989-08-10 Siemens Ag, 1000 Berlin Und 8000 Muenchen, De
US4936305A (en) * 1988-07-20 1990-06-26 Richards Medical Company Shielded magnetic assembly for use with a hearing aid
FR2634645A1 (en) * 1988-07-29 1990-02-02 Philips Ind Commerciale Hearing aid
EP0369624A3 (en) * 1988-11-16 1991-08-07 Richards Medical Company Trans-tympanic connector for magnetic induction hearing aid
DE3940632C1 (en) * 1989-06-02 1990-12-06 Hortmann Gmbh, 7449 Neckartenzlingen, De Hearing aid directly exciting inner ear - has microphone encapsulated for implantation in tympanic cavity or mastoid region
DE4104359C2 (en) * 1991-02-13 1992-11-19 Implex Gmbh, 7449 Neckartenzlingen, De
DE4104358C2 (en) * 1991-02-13 1992-11-19 Implex Gmbh, 7449 Neckartenzlingen, De
US5282858A (en) * 1991-06-17 1994-02-01 American Cyanamid Company Hermetically sealed implantable transducer
US5338287A (en) * 1991-12-23 1994-08-16 Miller Gale W Electromagnetic induction hearing aid device
DE4319599C1 (en) * 1993-06-14 1994-08-25 Siemens Audiologische Technik Hearing aid
US5772575A (en) * 1995-09-22 1998-06-30 S. George Lesinski Implantable hearing aid
DE69739101D1 (en) * 1996-03-25 2008-12-24 S George Lesinski Micro Threaded connections implantable hearing aid
DE69733837T2 (en) * 1996-05-24 2006-04-27 Lesinski, S. George, Cincinnati Improved microphones for implantable hearing aid
EP0912146B1 (en) * 1996-07-19 2009-11-18 Armand P. Neukermans Biocompatible, implantable hearing aid microactuator
US6940989B1 (en) * 1999-12-30 2005-09-06 Insound Medical, Inc. Direct tympanic drive via a floating filament assembly
US8147544B2 (en) 2001-10-30 2012-04-03 Otokinetics Inc. Therapeutic appliance for cochlea
US7421087B2 (en) * 2004-07-28 2008-09-02 Earlens Corporation Transducer for electromagnetic hearing devices
JP2007251643A (en) * 2006-03-16 2007-09-27 Jr Higashi Nippon Consultants Kk Sound transmission system
WO2008068724A1 (en) * 2006-12-06 2008-06-12 Nano Magic Technologies Sarl Invisible wireless earphones with rare earh magnet
WO2014205069A3 (en) * 2013-06-19 2015-02-26 Ototronix, Llc Improved method and apparatus for coil alignment in electromagnetic hearing implant
DE102013114771B4 (en) 2013-12-23 2018-06-28 Eberhard Karls Universität Tübingen Medizinische Fakultät In the ear canal hearing aid and hearing aid insertable system

Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3870832A (en) * 1972-07-18 1975-03-11 John M Fredrickson Implantable electromagnetic hearing aid
US4419995A (en) * 1981-09-18 1983-12-13 Hochmair Ingeborg Single channel auditory stimulation system
DE3243850A1 (en) * 1982-11-26 1984-05-30 Manfred Koch Induction coil for hearing aids for those with impaired hearing, for the reception of low-frequency electrical signals
US4467145A (en) * 1981-03-10 1984-08-21 Siemens Aktiengesellschaft Hearing aid
US4539440A (en) * 1983-05-16 1985-09-03 Michael Sciarra In-canal hearing aid
DE3431584A1 (en) * 1984-08-28 1986-03-13 Siemens Ag hearing aid
US4606329A (en) * 1985-05-22 1986-08-19 Xomed, Inc. Implantable electromagnetic middle-ear bone-conduction hearing aid device

Family Cites Families (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3209082A (en) * 1957-05-27 1965-09-28 Beltone Electronics Corp Hearing aid
US3764748A (en) * 1972-05-19 1973-10-09 J Branch Implanted hearing aids
BE833809A (en) * 1975-09-25 1976-03-25 hearing aid and method of examination and prosthetic correction of hearing
FR2365267B1 (en) * 1976-09-15 1982-03-19 France Etat
DE3225826A1 (en) * 1982-07-09 1984-01-12 Heyl Chem Pharm Annular skin implant and a process for the preparation thereof
CA1247960A (en) * 1983-03-24 1989-01-03 Hideki Aoki Transcutaneously implantable element
US4612915A (en) * 1985-05-23 1986-09-23 Xomed, Inc. Direct bone conduction hearing aid device

Patent Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3870832A (en) * 1972-07-18 1975-03-11 John M Fredrickson Implantable electromagnetic hearing aid
US4467145A (en) * 1981-03-10 1984-08-21 Siemens Aktiengesellschaft Hearing aid
US4419995A (en) * 1981-09-18 1983-12-13 Hochmair Ingeborg Single channel auditory stimulation system
DE3243850A1 (en) * 1982-11-26 1984-05-30 Manfred Koch Induction coil for hearing aids for those with impaired hearing, for the reception of low-frequency electrical signals
US4539440A (en) * 1983-05-16 1985-09-03 Michael Sciarra In-canal hearing aid
DE3431584A1 (en) * 1984-08-28 1986-03-13 Siemens Ag hearing aid
US4606329A (en) * 1985-05-22 1986-08-19 Xomed, Inc. Implantable electromagnetic middle-ear bone-conduction hearing aid device

Non-Patent Citations (12)

* Cited by examiner, † Cited by third party
Title
J. Fredrickson, D. Tomlinson, E. Davis and L. Odkvist, Evaluation of an Electromagnetic Implantable Hearing Aid, Canadian Journal of Otolaryngology, vol. 2, No. 1, 1973, pp. 53 62. *
J. Fredrickson, D. Tomlinson, E. Davis and L. Odkvist, Evaluation of an Electromagnetic Implantable Hearing Aid, Canadian Journal of Otolaryngology, vol. 2, No. 1, 1973, pp. 53-62.
J. Vernon, T. Mahoney, and A. Schlevning II, Implantable Hearing Aids, pp. 249 268. *
J. Vernon, T. Mahoney, and A. Schlevning II, Implantable Hearing Aids, pp. 249-268.
R. Goode and T. Glattke, Audition via Electromagnetic Induction, Arch Otolaryngol, Jul. 1973, pp. 23 26. *
R. Goode and T. Glattke, Audition via Electromagnetic Induction, Arch Otolaryngol, Jul. 1973, pp. 23-26.
R. Goode, An Implantable Hearing Aid, Tr. Am. Acad. Opth. & Otol., Jan. Feb. 1970, pp. 128 139. *
R. Goode, An Implantable Hearing Aid, Tr. Am. Acad. Opth. & Otol., Jan.-Feb. 1970, pp. 128-139.
W. Ruthen, C. Blitterswijk, C. Brenkman and J. Grote, Vibrations of Natural and Artificial Middle Ear Membranes Measured by a Squid Magnetometer. *
W. Ruthen, C. Blitterswijk, C. Brenkman and J. Grote, Vibrations of Natural and Artificial Middle-Ear Membranes Measured by a Squid Magnetometer.
W. Ruthen, M. Peters, C. Brenkman, H. Mol, J. Grote and L. van der Marel, The Use of a SQUID Magnetometer for Middle Ear Research, Cryogenics, Sep. 1982, pp. 457 460. *
W. Ruthen, M. Peters, C. Brenkman, H. Mol, J. Grote and L. van der Marel, The Use of a SQUID Magnetometer for Middle Ear Research, Cryogenics, Sep. 1982, pp. 457-460.

Cited By (78)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5015224A (en) * 1988-10-17 1991-05-14 Maniglia Anthony J Partially implantable hearing aid device
US4957478A (en) * 1988-10-17 1990-09-18 Maniglia Anthony J Partially implantable hearing aid device
US5259032A (en) * 1990-11-07 1993-11-02 Resound Corporation contact transducer assembly for hearing devices
US5425104A (en) * 1991-04-01 1995-06-13 Resound Corporation Inconspicuous communication method utilizing remote electromagnetic drive
US5913815A (en) * 1993-07-01 1999-06-22 Symphonix Devices, Inc. Bone conducting floating mass transducers
US5456654A (en) * 1993-07-01 1995-10-10 Ball; Geoffrey R. Implantable magnetic hearing aid transducer
US5554096A (en) * 1993-07-01 1996-09-10 Symphonix Implantable electromagnetic hearing transducer
US5624376A (en) * 1993-07-01 1997-04-29 Symphonix Devices, Inc. Implantable and external hearing systems having a floating mass transducer
US5857958A (en) * 1993-07-01 1999-01-12 Symphonix Devices, Inc. Implantable and external hearing systems having a floating mass transducer
US5800336A (en) * 1993-07-01 1998-09-01 Symphonix Devices, Inc. Advanced designs of floating mass transducers
US5897486A (en) * 1993-07-01 1999-04-27 Symphonix Devices, Inc. Dual coil floating mass transducers
US6676592B2 (en) 1993-07-01 2004-01-13 Symphonix Devices, Inc. Dual coil floating mass transducers
US6475134B1 (en) 1993-07-01 2002-11-05 Symphonix Devices, Inc. Dual coil floating mass transducers
US6071527A (en) * 1996-04-10 2000-06-06 Asahi Kogaku Kogyo Kabushiki Kaisha Deodorant microphone cover and method of producing the same
US5797834A (en) * 1996-05-31 1998-08-25 Resound Corporation Hearing improvement device
US6208740B1 (en) 1997-02-28 2001-03-27 Karl Grever Stereophonic magnetic induction sound system
US5993376A (en) * 1997-08-07 1999-11-30 St. Croix Medical, Inc. Electromagnetic input transducers for middle ear sensing
US6264603B1 (en) 1997-08-07 2001-07-24 St. Croix Medical, Inc. Middle ear vibration sensor using multiple transducers
WO1999053971A1 (en) * 1998-04-17 1999-10-28 University College London Bone implant
US6123660A (en) * 1998-09-03 2000-09-26 Implex Aktiengesellschaft Hearing Technology Partially or fully implantable hearing aid
US6689045B2 (en) 1998-09-24 2004-02-10 St. Croix Medical, Inc. Method and apparatus for improving signal quality in implantable hearing systems
US6277148B1 (en) 1999-02-11 2001-08-21 Soundtec, Inc. Middle ear magnet implant, attachment device and method, and test instrument and method
US6436028B1 (en) 1999-12-28 2002-08-20 Soundtec, Inc. Direct drive movement of body constituent
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DE3788529T2 (en) 1994-06-16 grant
CA1277761C (en) 1990-12-11 grant
EP0242038A3 (en) 1989-05-31 application
EP0242038B1 (en) 1993-12-22 grant
EP0242038A2 (en) 1987-10-21 application
DE3788529D1 (en) 1994-02-03 grant
JPS63159000A (en) 1988-07-01 application

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